Breastfeeding quantity estimator

ABSTRACT

A sensor for indirect estimation of breast milk intake by an infant, the sensor comprising: a housing configured to be externally attached to an incontinence product worn by a subject, said housing comprising: a light-emitting diode (LED) configured to illuminate the incontinence product; a photodetector configured to output an indication of the amount of light reflected from the incontinence product; and an integrated circuit configured to: (a) receive the indication from said photodetector, (b) compute, based on the indication, an amount of urine secreted by the subject into the incontinence product, and (c) estimate the amount of breast milk intake by the infant based on the amount of urine secreted by the subject into the incontinence product.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/177,803, filed Jun. 9, 2016, which is a continuation of U.S. patentapplication Ser. No. 14/692,306, which is a continuation ofInternational Application No. PCT/IL2013/050833, filed Oct. 16, 2013,which claims priority to U.S. Provisional Application No. 61/716,767,filed Oct. 22, 2012, the contents of which are hereby incorporated byreference in their entirety.

FIELD OF THE INVENTION

Some embodiments relate to a breastfeeding quantity estimator.

BACKGROUND

Breastfeeding is recommended by the American Academy of Pediatrics, theWorld Health Organization and medical professionals worldwide as thepreferred method for feeding infants during the first year of life.Human breast milk has significant health benefits that, to date, cannotbe replicated by infant formula. Specifically, breast milk has beenshown to reduce the incidence of infectious diarrhea, respiratoryinfections, otitis media, childhood obesity and other conditions.Breastfeeding has been shown to have health benefits for mothers too,such as by reducing the risk of postpartum bleeding and anemia. Risksare also lowered for ovarian and premenopausal breast cancer. Further,postpartum weight loss is enhanced in breastfeeding mothers. Otherbenefits of breastfeeding include its comforting effect upon both motherand infant. For these reasons, many health professionals feel thatbreastfeeding produces healthier, happier, infants and mothers, which iswhy breastfeeding is being promoted worldwide as a public healthmeasure.

The need to know the amount of breast milk suckled by an infant isimportant to many lactating mothers. This information may help evaluatethe infant's nutritional status, the need for breastfeeding guidance,and/or the use of infant formula, and is therefore important to thepediatrician as well. It is accepted that normal breast milk intake ofan average infant starts at a few dozen milliliters during its first dayof life, increases to a few hundred milliliters a day during the firstweek of life, and can reach approximately 700-900 milliliters per dayafterwards. See J. Riordan and K. Wambach, “Breastfeeding and HumanLactation”, Jones & Bartlett Publishers, 4^(th) ed. (2009).

Many mothers, due to their false impression and worry that insufficientmilk is consumed by the infant, choose to discontinue breastfeedingfully or partially, and start using formulas. This is an unfortunatesituation.

Devices for measuring the amount of milk expressed during breastfeedinghave been proposed in the past. Many such devices adopt methods of fluidflow measurement, and typically include a flow or capacity meter mountedon the breast during breastfeeding, to measure the amount of milkflowing through. A few examples of such devices are shown in U.S. Pat.No. 5,827,191 to Rosenfeld, U.S. Patent Application Publication No.2008/0039741 to Shemesh et al., and U.S. Patent Application PublicationNo. 2005/0177099 to Dahan. Other devices propose the use of flow gaugesutilizing ultrasound measurements or piezoelectric devices. Other thanaccuracy problems, it is assumed that such devices did not gain muchacceptance due to their intrusive nature, which interrupts the intimacyand simplicity of the mother/infant feeding and bonding process.

Other proposals include weighing the mother and/or infant or measuringthe fullness of the infant's stomach before and after nursing, asdisclosed, for example, in U.S. Patent Application Publication No.2008/0097169 to Long, et al., U.S. Patent Application Publication No.2008/0077040 to Ales, et al., and U.S. Patent Application PublicationNo. 2008/0077042 to Feldkamp, et al. Such proposals involve asubstantial degree of inconvenience, which may explain their lack ofwidespread acceptance. In addition, experimental data suggests thatweighing is an imprecise method for assessing milk intake in younginfants. See O. E. M. Savenije, P. L. P. Brand, “Accuracy and precisionof test weighing to assess milk intake in newborn infants”, Arch DisChild Fetal Neonatal (2006) 91:F330-F332.

Very commonly, pediatricians and nurses simply instruct worried mothersto count the number of wet (by urine) diapers per day, as someindication of the amount of breast milk suckled by the infant. 1-5 wetdiapers per 24 hours during the infant's first week of life, and 6 ormore wet diapers per 24 hours for older infants, is a rate commonlysuggested by caregivers as indicating sufficient breast milk intake.Naturally, however, this diaper counting cannot be regarded as exactscience, mainly since it does not provide a concrete measurement ofactual volume of urine secretion per 24 hours.

Accordingly, there is still a long felt need for unobtrusive, convenientdevices and methods of estimating the quantity of breast milk suckled byan infant.

Applicant's PCT Patent Application No. PCT/IB2012/052648, filed May 25,2012, discloses devices, systems and methods for sensing the well-beingof a subject, by detecting one or more physiological parameters.Applicant's PCT Patent Application No. PCT/IL2011/000615, filed Jul. 28,2011, discloses system and methods for monitoring physiologicalconditions of a subject. These patent applications are incorporatedherein by reference in their entirety.

SUMMARY

The following embodiments and aspects thereof are described andillustrated in conjunction with systems, tools and methods which aremeant to be exemplary and illustrative, not limiting in scope.

There is provided, in accordance with an embodiment, a sensor forindirect estimation of breast milk intake by an infant, the sensorcomprising: a housing configured to be externally attached to anincontinence product worn by a subject, said housing comprising: alight-emitting diode (LED) configured to illuminate the incontinenceproduct; a photodetector configured to output an indication of theamount of light reflected from the incontinence product; and anintegrated circuit configured to: (a) receive the indication from saidphotodetector, (b) compute, based on the indication, an amount of urinesecreted by the subject into the incontinence product, and (c) estimatethe amount of breast milk intake by the infant based on the amount ofurine secreted by the subject into the incontinence product.

There is further provided, in accordance with an embodiment, a urinesensor comprising: a housing configured to be externally attached to anincontinence product worn by a subject, said housing comprising: alight-emitting diode (LED) configured to illuminate the incontinenceproduct; a photodetector configured to output an indication of theamount of light reflected from the incontinence product; and anintegrated circuit configured to: (a) receive the indication from saidphotodetector, and (b) compute, based on the indication, an amount ofurine secreted by the subject into the incontinence product.

In some embodiments, said LED is a white-light LED.

In some embodiments, said LED is an infrared LED.

In some embodiments, said photodetector is a light-dependent resistor(LDR).

In some embodiments, the indication of the amount of light is a declinein voltage.

In some embodiments, the decline in voltage corresponds to an increasein the amount of urine in the incontinence product.

In some embodiments, the indication of the amount of light is anincrease in voltage.

In some embodiments, the increase in voltage corresponds to a decreasein hydration of the subject.

In some embodiments, said integrated circuit is further configured toestimate a hydration level of the subject, based on a detection of ashade of the urine secreted by the subject into the incontinenceproduct.

In some embodiments, said integrated circuit is further configured toestimate the hydration level of the subject based on a synergisticanalysis of the shade of the urine and the amount of the urine.

In some embodiments, said housing further comprises a sticker forexternal attachment to the incontinence product.

In some embodiments, said housing further comprises a Velcro forexternal attachment to the incontinence product.

In some embodiments, said housing further comprises a clip for externalattachment to the incontinence product.

In some embodiments, said housing further comprises a screen operativecouple to said integrated circuit, wherein said screen is configured todisplay the amount of urine.

In some embodiments, said housing further comprises a screen operativelycoupled to said integrated circuit, wherein said screen is configured todisplay the estimated amount of breast milk intake.

In addition to the exemplary aspects and embodiments described above,further aspects and embodiments will become apparent by reference to thefigures and by study of the following detailed description.

BRIEF DESCRIPTION OF THE FIGURES

Exemplary embodiments are illustrated in referenced figures. Dimensionsof components and features shown in the figures are generally chosen forconvenience and clarity of presentation and are not necessarily shown toscale. The figures are listed below.

FIG. 1 shows a characteristic layered diaper with a sensor according tosome embodiments;

FIG. 2 shows a cross-sectional view of layers forming that diaper;

FIGS. 3A-G show a front isometric view, a front plan view, a back planview, a right side view, a left side view, a top view and a bottom viewof an exemplary sensor, according to some embodiments.

FIGS. 4 and 5 show block diagrams of an electronic circuit of a sensor,according to some embodiments;

FIG. 6 shows a circuit diagram of a low-pass filter, according to someembodiments;

FIG. 7 shows an exemplary acoustic communication interface, according tosome embodiments;

FIG. 8 shows an acoustic interface of a sensing system, according tosome embodiments;

FIG. 9 shows a graphic interface, according to some embodiments;

FIGS. 10A, 10B and 10C show graphs of sensor readings, according to someembodiments; and

FIGS. 11A and 11B show graphs of sensor readings, according to someembodiments.

DETAILED DESCRIPTION

Devices and methods useful for indirect estimation of breast milk intakeby an infant are disclosed herein. According to present embodiments, theamount of urine secreted into the infant's diaper is measured, and maybe used to estimate if a sufficient amount of breast milk is suckled bythe infant. This estimation may be used instead of or together with thewet diaper counting method discussed above. The counting method may beenhanced if an indication of a wet diaper, and the amount of urine inthat wet diaper, is given, because if the infant's caregiver is unawareof these factors, he or she may change diapers only after a diaperaccumulates multiple urinations, leading to a false lower count of wetdiapers and to groundless worry.

Advantageously, the amount of urine is detected using a sensor which ismounted on the infant's diaper externally, and therefore does not comein direct contact with the urine or with the infant's body. Theadvantageous sensor allows for convenient, non-intrusive measurement ofurine secretion, in a manner which does not interfere with the intimacyand simplicity of the mother/infant feeding and bonding process. Inalternative embodiments, the sensor is embedded within the diaperitself.

In some embodiments, the sensor is used for measuring the amount ofurine secreted into an incontinence product, such as an adult diaper oran infant diaper, for purposes unrelated to breastfeeding. For example,the sensor may be used in scenarios requiring fluid management of asubject, to detect renal failure, to estimate hydration, and/or thelike.

According to some embodiments, the same or a different sensor,configured to estimate a subject's hydration level is provided. Thesensor detects the shade of the urine, which is known to be indicativeof the level of hydration. Generally, the darker the urine, the moredehydrated the subject is, and vice versa. Transparent urine usuallymeans a good hydration level. Optionally, the sensor also measures theamount of urine secreted, so that it estimates the level of hydrationusing a combination of two factors: amount and shade.

The terms “diaper”, “incontinence product” and “absorbent incontinenceproduct” may be used here interchangeably, and relate to a wearableproduct having a layered construction, which allows the transfer anddistribution of urine to an absorbent core structure where it is lockedin. Similarly, the term “infant” is used here for convenience only, andmay relate to any subject, such as a baby, a child or an adult.

Reference is now made to FIG. 1, which shows a characteristic layereddiaper 100 in a perspective view, and to FIG. 2, which shows across-sectional view of layers forming the same diaper. The basic layersfound in many modern diapers, such as diaper 100, are commonly: (a) anouter shell 102, commonly made of a breathable polyethylene film or anonwoven and film composite, which prevents wetness and soil transfer tothe outside environment; (b) an inner absorbent layer 104, usuallycontaining a mixture of air-laid paper and superabsorbent polymers; and(c) a layer 106 nearest the skin, oftentimes made of a nonwoven materialwith a distribution layer directly beneath, which transfers wetness tothe absorbent layer. A pair of fasteners 108 is commonly used to closethe diaper around the wearer's abdomen.

In some embodiments, a sensor, such as sensor 110, may be attached, asan external add-on, to outer shell 102 of diaper 100. In someembodiments (not shown), the sensor may be embedded in or integrallyformed with outer shell 102. In some embodiments (not shown), the sensormay be embedded in or integrally formed with inner absorbent layer 104.In some embodiments, the one or more sensors may be embedded in orintegrally formed with the layer 106 nearest the skin. The positioningof sensor 110 is shown here merely as an example. A sensor maynonetheless be positioned in or on any of the diaper's layers, and/or ata different area of the diaper; in addition, components of the sensormay be distributed in different layers and/or in different positions.

A photodetector may be used, in the sensor, for measuring the amount ofurine secreted into a diaper. There are multiple varieties ofphotodetectors (also “light sensors”) which may be suitable, such asphotoresistors (LDRs), photovoltaic cells, photodiodes (operative inphotovoltaic mode or photoconductive mode), IR sensor, phototransistors,CCD (charge coupled device), CMOS (complementary metal oxidesemiconductor) and/or the like.

An exemplary sensor 300, for use in infants and/or other persons in needthereof, is shown in FIGS. 3A-G in a front isometric view, front planview, back plan view, right side view, left side view, top view andbottom view, respectively. Sensor 300 may include a housing encompassinginternal components, such as a photodetector, an illuminator (e.g. LED),an integrated circuit (IC) and/or the like. The housing may be attachedto the wearer's garment, such as a diaper, by way of a sticker, Velcroand/or the like, which may be positioned, for example, on the back sideof the housing. Additionally or alternatively, the housing may beattached to the garment using a clip and/or other means known in the art(not shown).

The IC of sensor 300 may measure the amount of urine secreted into adiaper, using, for example, a photodetector, as discussed above. Thephotodetector outputs an indication of the amount of light reflectedfrom the diaper. The indication is received by the IC which computes theamount of secreted urine based on the indication. The photodetector mayreceive light through an aperture in the housing, and the LED, which isoptional, may illuminate the garment through an optional LED aperture.One or both apertures may be open, or closed with a cover transparentenough to allow the transfer of light. Namely—the apertures arevisually-exposed at the back side of the housing. The cover may be, forexample, the Velcro, adhesive or a different means for attaching sensor300 to the garment. An optional IR transceiver may be positioned at ornear an IR hole.

It should be noted that some or even all sensors, transceivers,illuminators and/or the like may be positioned under the Velcro,adhesive or the different means for attaching sensor 300 to the garment,or even inside the housing with no exposure to the environment. This mayprovide protection for the sensors/illuminators while avoiding the needto provide visible holes in the housing. It may also provide sealing ofthe housing, either completely or partially.

The LED may be a white-light LED, a red-light LED, an infra-red LED or aLED of a different wavelength.

A screen of sensor 300 may be operatively coupled with the IC, toindicate the amount of urine measured and/or the amount of breast milkintake. The amount of breast milk intake indicated by the screen may beequal, as one example, to the amount of urine; these two amounts areknown to be similar. Additionally or alternatively, the IC may displayon the screen a simple indication of a urination event, in the form ofan alert. The alert may be issued when the sensor detects at least apredetermined amount of urine, e.g. at least 10 cc, at least 15 cc, atleast 20 cc, at least 30 cc or any other predetermined amount programmedinto the IC.

The alert may indicate to a caregiver that the subject wearing thediaper has urinated. The caregiver may then use the wet diaper countingmethod discussed above, to know if the breast milk intake by the subjectis sufficient. The indication on the screen may be, for example,numerical—showing the number of milliliters (or a different unit)measured. Additionally or alternatively, a multi-level scale may bedisplayed, where each level in the scale is indicative of a differentamount of urine. Additionally or alternatively, sensor 300 may include aspeaker, a buzzer, and/or the like, for issuing audible indication ofthe amount of urine.

Alternatively or additionally, the alert may indicate to a caregiverthat the hydration level of the subject wearing the diaper has fallenbelow a threshold level. The alert may be issued when the sensor detectsat least a predetermined shade of urine programmed into the IC.

Voltage fluctuations in the output of the photodetector, resulting fromthe infant's movement and activity, may make the urine amountmeasurement more complex. Advantageously, software and hardware low-passfilters (LPFs) incorporated in the IC, which were tested separately,were able to make the signal outputted by the photodetector moreparabolic and softer, making the urine amount measurement possible usingthe methods and algorithms discussed here. The LPFs were based on amoving average calculation. FIG. 5 shows an alternative to FIG. 4, usingLPFs. FIG. 6 shows an exemplary 2^(nd)-order LPF circuit, although thoseof skill in the art will recognize that an LPF of a different orderand/or topology may be suitable.

Reference is now made back to FIGS. 3A-G. Optionally, sensor 300includes a piezoelectric sensor (not shown) for detecting the breathingof the wearer. The piezoelectric sensor may be a PVDF sheet positionedinside or external to the housing, advantageously without contacting thewearer's body directly, and optionally not even through any flexiblemember, such as a membrane, which is sometimes used in the art formechanically transferring motion or pressure from an object to a PVDFsheet. The PVDF sheet may be located, for example, on the internalsurface of the back side of the housing. The PVDF sheet is optionally incontact with the housing. Alternatively, the PVDF sheet may be mountedinside the housing without contacting it. Further alternatively, aslightly depressed area in the housing may house the PVDF sheetexternally to the housing, which depressed area may be covered by theVelcro, adhesive or the like as discussed above.

Sensor 300 may further include a potty training functionality,configured to enhance the common infant potty training procedure. Aparent or another caregiver may record one or more voice messages, inhis or hers own voice, to be automatically played using a speaker whensensor 300 senses secretions. The voice message(s) may, for example,remind the infant that the potty should have been used, therebyproviding immediate biofeedback to unintentional secretion. Optionally,to make sensor 300 more appealing to the infant, it may automaticallyplay a pre-recorded voice message when touched by the infant.

Voice messages may be pre-recorded in the factory and/or recorded by theparents/caregivers. To that end, one or more buttons, such as a recordbutton and/or a play button may be provided in sensor 300. Optionally,one or more status lights and/or a screen (such as an LCD screen) maysignal to the person recording that the recording has begun, endedand/or the like.

Optionally, either before, after or during the playing of any of suchvoice message, an acoustic signal may be emitted by sensor 300, totransmit an indication of the detected secretion to a remote orreceiving device, as will be discussed below. Further optionally, theindication may trigger the loading and/or playing of an educationalvideo clip on potty training on the remote or receiving device, whichthe parent and child can watch together or separately.

Further optionally, a potty may include an acoustic or a radio frequencyreceiver, so that when an indication of a fecal and/or urinary secretionevent is received at the potty, the potty may urge the infant to use it,by emitting light, sound and/or the like. The indication may be receivedfrom sensor 300 and/or from the remote or receiving device.

According to some embodiments, the sensor disclosed herein may furtherinterface and/or communicate with an external and/or remote device toconvey a signal generated by the sensor(s) disclosed herein to thedevice (herein, a “receiver” or a “receiving device”). Conveying thesignal from the sensor of the sensing device to the receiving device maybe performed by various communication routes, such as radio frequency oracoustic communication.

Acoustic communication makes use of sound and/or ultrasound, whereby a“transmitter” produces a sound that is detected by a “receiver”. Soundis produced by the transmitter when a physical object vibrates rapidly,disturbs nearby air molecules (or other surrounding medium) andgenerates compression waves that travel in all directions away from thesource. Sound can be made to vary in frequency (high pitch vs. lowpitch), amplitude (loudness), and periodicity (the temporal pattern offrequency and amplitude). Since acoustic waves move rapidly through themedium, acoustic signals can be quickly started, stopped, or modified tosend a time-sensitive message.

According to some embodiments, for each of the various physiologicalconditions detected by the sensing devices and systems as disclosedherein, a different acoustical signal may be generated by one or moretransducers connected to the microcontroller. The various acousticalsignals may differ by various parameters, such as, but not limited to:frequency, periodicity, amplitude, duration, series of signals and theintervals therebetween (duty cycle) and/or the like. The frequency ofthe acoustic alert may be in any range. In an embodiment, the acousticalert is in the range of 1 Hz to 10 KHz. In another embodiment, theacoustic alert is in the range of 10 Khz to 18 Khz. In anotherembodiment, the acoustic alert is in the range of 18 KHz to 20 Khz. Inanother embodiment, the acoustic alert is in the range of 18 KHz to 22Khz. In another embodiment, the acoustic alert is in the range of 20 KHzto 22 Khz. In another embodiment, the acoustic alert is higher in theultrasonic range, such as above 22 KHz.

For example, if the device's sensor detects urine, it may produce an 8KHz tone, optionally in conjunction with other series of tones. Forexample, if the device sensor detects feces, it may produce an 8 KHztone, optionally in conjunction with other series of tones. As anotherexample, if the device's sensor detects high temperature it may producea 5 Khz tone, optionally in conjunction with other series tones. As yeta further example, if the device's sensor detects a breathing problem,it may produce a 20 Khz tone, optionally in conjunction with otherseries of tones. These were simplistic examples, meant merely todemonstrate how acoustic communication may be realized.

According to further embodiments, the acoustical signal produced by thesensing device may be received by a receiving device, which is equippedwith a microphone. Various acoustic communication protocols may be usedfor establishing an acoustic communication between the transmitter (thesensor) and the receiving device. For example, a publication entitled“Multi-User Frequency Hopping Underwater Acoustic CommunicationProtocol”, Woods Hole Oceanographic Institution, Woods Hole, Mass.02543, May 25, 2000, the contents of which is incorporated by referencein their entirety, discloses an exemplary acoustic communicationprotocol in which data “packets”, similar in concept to those used in IPcommunications, are produced using acoustic waves.

According to some embodiments, the receiving device may include any typeof device configured to receive an acoustic signal via the appropriateacoustic communication protocol, and may further convey the signal to auser, who may be located in a remote location. An added benefit of sucha setting is that acoustic communication, unlike radio frequencycommunication, does not involve electromagnetic radiation in thesubject's area, thereby increasing the safety of use of the devices andsystems disclosed herein.

According to some embodiments, the acoustic tone or set of tones whichmay be generated by the sensing device define an acoustic protocol inthe time domain. In some embodiments, the protocol may be programmed inthe sensing device's microcontroller and in the receiving device.

According to some embodiments, an exemplary acoustic protocol mayinclude the following “packets”: (1) start bit, get ready for tonesequence; (2) first tone; (3) second tone; (4) N^(th) tone; (5) stopbit, tone sequence stopped. Any of the steps and the time length, numberof bits and frequency of the bit tone, loops, and the like, may bechanged to define an appropriate protocol.

Reference is now made to FIG. 7, which schematically illustrates anexemplary acoustic communication interface between a sensing device anda receiving device. Sensing device 2600 includes an audio encoder 2602,adapted to produce an acoustic signal based on the signal produced bythe sensor. Audio encoder 2602 may be incorporated in themicrocontroller discussed earlier, or be connected to it. The sensingdevice further includes a transducing element 2604, adapted to convertan electrical signal from audio encoder 2602 into an acoustic signaltransmitted towards the remote receiver. In some exemplary embodiments,the transducing element 2604 is a speaker. The acoustic signal producedby the sensing device may then be detected by transducer unit 2612 ofreceiving device 2610. In some exemplary embodiments, transducer 2612 isa microphone. The acoustic signal may then be decoded by audio decoder2614 of the receiving device. Decoding the acoustic signal may be usedto convert the acoustic signal to an electrical signal. The decodedsignal may be processed and conveyed to a user. In some embodiments, thedecoded signal may be converted to an alarm signal that may a visualsignal, a tactile signal, an audible signal, and the like, or anycombination thereof.

According to some embodiments, the receiving device may be portable. Insome embodiments, the receiving device may be placed in the vicinity ofthe sensing device. In some embodiments, the receiving device may beplace at a remote location, but still in acoustic communication rangefrom the transmitting device. In some exemplary embodiments, thereceiving device is a smart phone. In some exemplary embodiments, thereceiving device is configured to communicate with a smart phone.

Reference is now made to FIG. 8, which schematically illustrates anacoustic interface of a sensing system, according to some embodiments.As shown in FIG. 8, in a system 2700, a sensing device 2702 is placed ona subject (exemplary baby 2704). When an event is detected by the sensorof the sensing device, an acoustic alert is produced by the sensingdevice. The acoustic alert is detected by a receiving device such asreceiving device 2706, which is located in the proximity of the subject.The receiving device may then issue an alert (such as audible, tactileand/or visual alert) to a supervisor. Additionally or alternatively, thereceiving device may serve as a relay station configured to communicatewith a remote device (such as smart phone 2708), which is, in turn,configured to generate an appropriate alarm to the supervisor.

In some embodiments, the receiving device is configured to communicatewith the remote device via the Internet and/or via short-range radio,utilizing technologies such as WiFi, Bluetooth, SMS, cellular datacommunication, push notification protocol, and activate the alarmtherein, in order to notify a supervisor which may be located in aremote location. The remote device may execute an application forcommunicating with the receiving device and to produce audible and/orvisual alarm and/or tactile alarms.

In an implementation successfully experimented with by the inventor, anApple iPhone 4 smart phone (hereinafter “iPhone”) was used as thereceiving device. The iPhone's microphone picked up the acoustic signalswhich were emitted by the sensing device from a range of approximately10 meters with no walls in between or from a lower range if wallsexisted, and then transmitted an alert via Apple's push notificationservice (APN) to another iPhone acting as the remote device.

The Apple Push Notification service is intended to relay messages toiDevices even when a target application on the receiving device is notrunning. The APN transports and routes a notification from a givenprovider to a given device. A notification is a short message consistingof two major pieces of data: the device token and the payload. Thedevice token contains information that enables the APN to locate thedevice on which the client application is installed. The APN also usesit to authenticate the routing of a notification. The payload is aJSON-defined property list that specifies how the user of an applicationon a device is to be alerted. The flow of remote-notification data isone-way. The provider composes a notification package that includes thedevice token for a client application and the payload. The providersends the notification to the APN which, in turn, pushes thenotification to the device.

The message received by the iPhone acting as the remote device includedinformation describing the event detected by the sensing device. Theuser was provided with the option of triggering the opening of theinventor's mobile application installed on this iPhone, which displayedthe alert more visually. The application produced an audible, a tactileand/or a visual alarm. In some embodiments, the visual alarm is agraphical animation (shown for example in FIG. 9). For example, if urineis detected by the sensing device, an appropriate acoustic signal isgenerated. The acoustic signal is received by the receiving device (suchas, for example, a smart phone, 2800) in which a visual and audioalarms, in the form of an animation of a diaper, changes its color toblue (2802), in conjunction with water/splash sound are produced by thesmart phone. Additionally or alternatively, the receiving device mayrelay information regarding the detection to the remote device, in whicha visual and audio alarms are activated. As another example, if fecesare detected, a visual and audio alarms in the form of an animation of adiaper changes its color to brown, in conjunction with gas sounds areproduced by the smart phone. For example, if high body temperature isdetected by the sensing device, a visual and audio alarms in the form ofan animation of a thermometer changing its color to green (2804) inconjunction with boiling sound is produced. Finally, if a breath rateproblem is detected by the sensing device, a visual and audio alarm inthe form of an animation of a still heart (2806) in conjunction withambulance sound is produced.

More details on Apple's Push Notification service and related issues isavailable online at Apple's iOS Developer Library,http://developer.apple.com/library/ios/navigation/, which isincorporated herein by reference in its entirety.

EXAMPLES AND EXPERIMENTAL RESULTS

In a series of experiments conducted by the inventor, the measurement ofurine amount in a diaper, as well as the detection of urine shade in adiaper, have been tested and verified. The experiments discussed belowinclude devices and methods which form embodiments of the presentinvention.

In a first experiment, a sensor including an LDR and a LED illuminatorwas used. The LDR was PerkinElmer Optoelectronics VT900. However, LDRsof different models are explicitly intended herein. Optionally, the LDRin some embodiments is configured to sense light in approximately thevisible spectrum, also referred to as “ambient light”. The illuminator,namely—the LED in this example, is an essentially white LED. The sensorwas attached externally to a Pampers Active Baby size 3 diaper worn by ababy-shaped doll. The sensor was attached to the front area of thediaper, over the lower abdomen of the doll. The experiment was repeatedthree times: once with injection of 10 milliliters (ml) of water intothe diaper, once with injection of 20 ml, and once with injection of 30ml. Sensor readings were approximately linearly correlated with theamount of water, which simulated urine. FIGS. 10A, 10B and 10C showgraphs of sensor readings for the 10 ml, 20 ml and 30 ml injections,respectively. The Y-axis in these figures denotes voltage output of thephotodiode, and the X-axis denotes time in minutes and seconds. Asshown, the injecting of water (equivalent to urination) results in arapid decline in voltage. In the 10 ml injection, the voltage differencebetween a pre-injection baseline and a plateau reached betweenapproximately 30 seconds and 120 seconds post-injection, was 11millivolt (mV). In the 20 ml injection, the difference was 38 mV, and inthe 30 ml injection 68 mV. In other words, each 10 ml addition from theinitial 10 ml is exhibited, essentially linearly, in an additional dropof about 30 mV.

In a second experiment, a sensor including an IR sensor was used. The IRsensor was a Fairchild QRE1113GR.

The IR sensor was attached externally to a Pampers Active Baby size 3diaper worn by a baby-shaped doll. The sensor was attached to the frontarea of the diaper, over the lower abdomen of the doll. The experimentwas repeated multiple times, with injection of liquids imitating urineof different shades—from clear (water) to relatively dark yellow (applesyrup). FIGS. 11A and 11B show graphs of sensor readings for clear (purewater) liquid injection and of dark yellow (apple syrup) liquidinjection, respectively. The Y-axis in these figures denotes voltageoutput of the photodiode, and the X-axis denotes time in minutes andseconds. As shown, the injecting of either liquid results in a rapidincrease in voltage, followed by a slower decay. The difference betweenthe pre-injection baseline and a post-injection peak (which occurredafter about 1 minute) was 1.382 Volts for the water, and 0.637 Volts forthe apple syrup.

In additional experiments (graphs thereof are not shown), intermediatelevels of liquid darkness were used, resulting in approximately linearchanges in voltage. In conclusion, this method is reliable indetermining the hydration level of a subject based on his or her urineshade.

Another example for a suitable sensor adapted to detect the shade ofurine is a TCS3404 digital color sensor by Texas Advanced OptoelectronicSolutions, Inc. The TCS3404 includes an 8×2 array of filteredphotodiodes, analog-to-digital converters, and control functions on asingle monolithic CMOS integrated circuit. Of the 16 photodiodes, 4 havered filters, 4 have green filters, 4 have blue filters, and 4 have nofilter (clear).

Yet a further example of a suitable sensor adapted to detect the shadeof urine is the ALS-PT19-315C ambient light sensor manufactured byEverlight Electronics Co., Ltd.

Optionally, a sensor for urine quantity measurement and a sensor forurine shade measurement are used together, in a same housing, so as toboth indicate the amount of secreted urine and the hydration level.Alternatively, a single sensor, whose voltage (or other) readings areindicative of both urine quantity and shade, may be used.Advantageously, knowing both the urine's quantity and its shade enablesa processor of the sensor(s) to synergistically analyze estimate thelevel of hydration. For example, if the urine's shade is relativelydark, but its amount over a certain duration is relatively large, thenit is likely that the subject is not substantially dehydrated. Incontrast, a small quantity of light-colored urine may still beindicative of dehydration.

Some embodiments may be implemented, for example, using a non-transitorycomputer-readable medium or article which may store an instruction or aset of instructions that, if executed by a sensor comprising a hardwareprocessor, cause the sensor to perform a method and/or operations inaccordance with embodiments of the invention. Such a sensor may include,for example, any suitable processing platform, computing platform,computing device, processing device, computing system, processingsystem, computer, processor, or the like, and may be implemented usingany suitable combination of hardware and/or software. Thecomputer-readable medium or article may include, for example, any typeof disk including floppy disks, optical disks, CD-ROMs, magnetic-opticaldisks, read-only memories (ROMs), random access memories (RAMs)electrically programmable read-only memories (EPROMs), electricallyerasable and programmable read only memories (EEPROMs), magnetic oroptical cards, or any other type of media suitable for storingelectronic instructions, and capable of being coupled to a computersystem bus.

The instructions may include any suitable type of code, for example,source code, compiled code, interpreted code, executable code, staticcode, dynamic code, or the like, and may be implemented using anysuitable high-level, low-level, object-oriented, visual, compiled and/orinterpreted programming language, such as C, C++, C#, Java, BASIC,Pascal, Fortran, Cobol, assembly language, machine code, or the like.

In the description of the application, each of the words “comprise”,“include” and “have”, and forms thereof, are not necessarily limited tomembers in a list with which the words may be associated.

What is claimed is:
 1. A device, comprising: a housing configured to beexternally attached to an incontinence product worn by a subject,wherein the housing comprises either: (a) a first sensor comprising: (i)a first light-emitting diode (LED) configured to illuminate a firstportion of the incontinence product; (ii) a first photodetectorconfigured to output an indication of an amount of light reflected fromthe first portion of the incontinence product illuminated by the firstLED; and (iii) a first integrated circuit, configured to receive anindication from the first photodetector, and compute, based on theindication from the first photodetector, an amount of urine in theincontinence product; or (b) a second sensor comprising: (i) a secondlight-emitting diode (LED) configured to illuminate a second portion ofthe incontinence product; (ii) a second photodetector configured tooutput an indication of the amount of light reflected from the secondportion of the incontinence product illuminated by the second LED; and(iii) a second integrated circuit, configured to receive an indicationfrom the second photodetector, and compute, based on the indication fromthe second photodetector, a hydration level of the subject; or (c) bothsensors (a) and (b).
 2. The device of claim 1, wherein the subject is aninfant.
 3. The device of claim 2, wherein the device provides anindirect estimate of breast milk intake by the infant.
 4. The device ofclaim 2, wherein the first integrated circuit is further configured toissue an alert if the amount of urine in the incontinence productexceeds a pre-determined threshold, thereby confirming adequate breastmilk intake by the infant.
 5. The device of claim 1, wherein the firstLED is a white-light LED.
 6. The device of claim 1, wherein the secondLED is an infrared LED.
 7. The device of claim 1, wherein the firstphotodetector is selected from the group consisting of: photoresistors,photovoltaic cells, photodiodes, infrared sensors, phototransistors,CCDs (charge coupled devices), and CMOS (complementary metal oxidesemiconductors).
 8. The device of claim 7, wherein the firstphotodetector is a light-dependent resistor (LDR).
 9. The device ofclaim 1, wherein the second photodetector is selected from the groupconsisting of: photoresistors, photovoltaic cells, photodiodes, infraredsensors, phototransistors, CCDs (charge coupled devices), and CMOS(complementary metal oxide semiconductors).
 10. The device of claim 9,wherein the second photodetector is a light-dependent resistor (LDR).11. The device of claim 1, wherein the housing further comprises ascreen operatively coupled to the first integrated circuit, wherein thescreen is configured to display the amount of urine in the incontinenceproduct.
 12. The device of claim 1, wherein the housing furthercomprises a screen operatively coupled to the second integrated circuit,wherein the screen is configured to display the hydration level of thesubject.
 13. The device of claim 1, wherein the housing furthercomprises a screen operatively coupled to the first and secondintegrated circuit, wherein the screen is configured to display theamount of urine in the incontinence product and the hydration level ofthe subject.
 14. The device of claim 3, wherein the housing furthercomprises a screen operatively coupled to the second integrated circuit,wherein the screen is configured to display the amount of breast milkintake of the infant.